Ultrasonic transducer probe with axisymmetric lens

ABSTRACT

According to the present invention, an ultrasonic transducer probe is provided having an array of ultrasonic transducers rotatably mounted about an axis within the ultrasonic transducer probe, a lens mounted to the array, and a housing encasing the array and the lens. The lens is symmetric about the axis of rotation of the array. In addition, the housing has a continuous upper surface that is formed, in a region adjacent to the symmetric lens, to mate with the symmetric lens.

BACKGROUND OF THE INVENTION

The invention relates to ultrasonic imaging systems, and more particularly to systems that utilize an acoustic lens to focus ultrasonic energy.

The users of medical ultrasonic transducer probes, hereinafter referred to as sonographers, can obtain images of a region within a body by properly positioning a probe against the body. In order to obtain images having diagnostic value, the sonographer may have to physically manipulate the position of the probe by sliding, rotating, and tilting the probe. One area in particular where this manipulation is more challenging is transesophageal cardiac imaging. During transesophageal cardiac imaging, the sonographer positions a transducer housing at the tip of the probe against the esophagus or stomach of a patient in order to obtain different fields of view of the heart.

Typically for this application, the transducer housing contains a number of acoustic transducer elements, which may be sequentially electrically excited by an ultrasound control and operating system to obtain an image in an object plane that is perpendicular to the transducer housing and the transducer elements. It has been found desirable to rotate the transducer elements contained within the transducer housing independently from the physical manipulation of the housing itself. In combination with the ability to slide, rotate and tilt the transducer housing, the ability to independently rotate the transducer elements within the housing gives the sonographer the ability to obtain an ultrasonic image of any or all object planes orthogonal to the upper surface of the transducer elements at each location to which the housing can be moved.

Because the transducer housing on this type of probe may be placed within the body of the patient being examined, it must be sealed to protect against the ingress of bodily fluids, sterilant solutions, and cleaning solutions. The seal may also prevent moving parts, such as the rotating transducer elements, from contacting the body of the patient.

The acoustic energy radiated from the transducer housing may be focused by mounting an acoustic lens to the transducer elements within the housing. A cylindrical lens, which does not vary in thickness along the azimuthal direction, is sometimes used to provide a fixed focus to the transducer array in the elevation direction.

Devices are known that utilize a cylindrical lens. For example, U.S. Pat. No. 5,127,410 to King et al. includes a compound lens secured on top of a rotatable transducer. The compound lens may have a convex cylindrical lens of a first material mated to a concave lens of a second material. The second material has substantially the same acoustic properties as the body being scanned. The concave portion of the compound lens is shaped so that the upper surface of the compound lens is flat. The flat upper surface of the compound lens is mated to a flat lens assembly that seals an opening in the transducer housing. The opening is sealed, for example by a thin plastic film that is bonded to the housing in the area around the opening. A backing layer is formed to the plastic film and an RFI screen is embedded in the backing layer. A grease layer lubricates the interface between the flat upper surface of the compound lens and the flat lens assembly that seals the transducer housing.

A disadvantage of the King device is that a number of material layers are added to the top of the transducer elements, which can cause degraded performance due to attenuation within the layers or reflections at the material interfaces giving rise to reverberation artifacts in the resultant image. In addition, the concave lens may be difficult to fabricate. Few solid materials possess the acoustic properties required of the concave lens, and those materials that do possess the required properties may not adhere to the convex lens material and may absorb certain grease or oil materials causing the concave lens to expand. Expansion of the concave lens may lead to distortion of the transducer housing's component parts, unreliability, and a reduction in image quality. Furthermore, the added process steps in fabricating and assembling each material layer may decrease yield.

A further disadvantage of the King device is that the compound lens may require more space within the transducer housing than would a simple lens. It is desirable to minimize the size of the transducer housing so that it may be easily inserted by the sonographer and manipulated within the body of the patient without causing excessive patient discomfort.

A further disadvantage of the King device is that the flat lens assembly that seals the opening in the transducer housing may deform or make poor contact with the body of the patient upon application of pressure by the sonographer. It is desirable to maintain acoustic contact with the body of the patient because the presence of any gaps between the transducer housing and the patient will seriously degrade performance.

A still further disadvantage of the King device is that additional process steps are required to seal the opening in the housing and the seal may introduce additional material layers between the transducer elements and the body of the patient. As noted above, it is desirable to minimize the number of material layers between the transducers and the patient and to minimize processing steps in constructing the transducer housing.

Accordingly, it would be desirable to have an improved ultrasonic transducer probe.

SUMMARY OF THE INVENTION

According to a first aspect of the present invention, an ultrasonic transducer probe is provided having an array of ultrasonic transducers mounted within the ultrasonic transducer probe, a lens mounted to the array, and a housing encasing the array and the lens. The housing has a continuous surface adjacent to the lens.

According to a second aspect of the present invention, an ultrasonic transducer probe is provided having an array of ultrasonic transducers rotatably mounted about an axis within the ultrasonic transducer probe, a lens mounted to the-array, and a housing encasing the array and the lens. The lens is symmetric about the axis of rotation of the array. In addition, the housing has a continuous upper surface that is formed, in a region adjacent to the symmetric lens, to mate with the symmetric lens.

According to a third aspect of the present invention, an ultrasound system for providing diagnostic information from the interior of a body is provided having an ultrasonic transducer probe, an operating and control system for processing electrical signals produced by the ultrasonic transducer probe, and means for operatively coupling the ultrasonic transducer probe to the operating and control system.

The transducer probe has an array of ultrasonic transducers, an axisymmetric lens mounted to the array, and a housing encasing the array and the lens. The housing has a continuous surface adjacent to the lens.

According to a fourth aspect of the present invention, a method of providing diagnostic information from the interior of a body is provided having the steps of providing an ultrasound system having transmitting electronics, receiving electronics, an array of ultrasonic transducer elements and an axisymmetric lens attached to the array, storing values corresponding to a propagation time through the axisymmetric lens and an angle of refraction at an interface between the lens and the body for a set of acoustic lines, adjusting the transmitting electronics and the receiving electronics in accordance with the stored values, and transmitting acoustic pressure waves into the body and receiving acoustic echoes from the body through the axisymmetric lens on the set of acoustic lines.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A through 1C are sectional views of a transducer probe in accordance with the present invention.

FIG. 2 is an isometric view of an upper surface of a transducer housing of the probe of FIG. 1.

FIG. 3 is a sectional view along the azimuthal axis of an ultrasonic transducer array and a lens as shown in the probe of FIG. 1.

FIG. 4 illustrates an image plane formed by scanning a transducer array in a variable vertex format.

FIGS. 5A and 5B illustrate an acoustic scan line emanating from a vertex and propagating through a constant sound velocity medium and an axisymmetric lens, respectively.

DETAILED DESCRIPTION OF THE PRESENTLY PREFERRED EMBODIMENTS

The present invention is best understood by reference to the embodiments shown in FIGS. 1 to 5 where like elements are referred to by like numerals. FIG. 1A shows a transducer housing 2 containing a rotating transducer array 4. A lens 6 is positioned adjacent to the transducer array 4. Preferably, the lens 6 is symmetric about an axis of rotation 8 of the transducer array 4. Lenses having the property of being symmetric about an axis of rotation are referred to herein as axisymmetric lenses. Parabolic lenses, spherical lenses, and hyperbolic lenses are examples of axisymmetric lens.

As shown in FIGS. 1A and 2, the transducer housing 2 has a continuous surface 10 adjacent to the axisymmetric lens 6. In the region of the housing 2 that is adjacent to the lens 6, the continuous surface 10 of the transducer housing 2 is formed into a window 12. The window 12 mates to the shape of the lens 6. Preferably, the window 12 is integrally formed with the transducer housing 2, as shown in FIGS. 1 and 2. In the embodiment shown in FIG. 1, the radii of curvature of the window 12 match the radii of curvature of the axisymmetric lens 6.

A thin layer of a grease 14 fills an interface within the transducer housing 2 between the window 12 and the axisymmetric lens 6. The grease 14 lubricates the interface between the window 12 and the axisymmetric lens 6 and displaces air that would otherwise occupy the interface.

The transducer array 4 is mounted on a backing material 16, which is acoustically attenuative. A preferred acoustically attenuative backing material is described in U.S. Pat. No. 5,297,553 issued to Sliwa, Jr. et al., which is incorporated herein by reference. Preferably, the backing material 16 is formed from rigid polymeric or polymer-coated particles fused into a macroscopically rigid structure having remnant tortuous permeability, as shown in U.S. Pat. No. 5,297,553. This structure provides high acoustic attenuation and permits fluid passage into the backing structure during fabrication. An optional container may provide additional physical integrity to the backing material 16, and the backing material 16 may be attached to the container by an optional bonding adhesive layer. The backing materials described in U.S. Pat. No. 5,297,553 provide high acoustic attenuation. This allows a thinner backing material to be used, thereby allowing the transducer probe to be downsized.

A rotatable cable 18 projects into the transducer housing 2, as shown in FIGS. 1A-1C. Affixed to a distal end of the rotatable cable 18 is a worm 20. The worm 20 engages a worm wheel 22, as shown in FIG. 1B. The worm wheel 22 is attached via a vertical shaft 24 to a gear 26. As shown in FIG. 1C, the gear 26 engages an idler gear 28, which in turn engages a ring gear 30 attached to a turntable base 32. The turntable base 32 is attached to a pedestal 34 for a platform 36. The platform 36 supports the backing material 16, the transducer array 4, and the axisymmetric lens 6. A stationary pin 38, which is attached at one end to the transducer housing, projects into the pedestal 34.

The platform 36, the pedestal 34, and the turntable base 32 form a bobbin-like structure. A number of ball bearings 40 are contained within the pedestal 34. Preferably, the platform 36 and the pedestal 34 containing the bearings 40 is a single-piece assembly fabricated from hardened stainless steel.

A flexible circuit 42 wraps around and is anchored to the pedestal 34. The flexible circuit 42 electrically couples the transducer array 4 to a remote ultrasound control and operating system. Preferably, the flexible circuit 42 is directly coupled to the elements of the transducer array 4.

During operation of the transducer probe shown in FIGS. 1 and 2, the transducer array 4 and the axisymmetric lens 6, which is secured thereto, may be rotated by a sonographer or the ultrasound control and operating system coupled to the transducer probe. The housing 2, including the integral window 12, which is in contact with the body of the patient, typically remains stationary during rotation of the array 4 and lens 6.

Rotation of the transducer array 4 and the axisymmetric lens 6 may be brought about by turning the rotatable cable 18, which operates as a worm drive for the gears 26, 28 and 30 coupled to the turntable base 32. During rotation, the layer of grease 14 lubricates the sliding interface between the axisymmetric lens 6 and the window 12 of the housing 2 and ensures that the interface remains void free. Preferably, the turning force applied to the rotatable cable 18 is generated mechanically, such as by an electric motor. Alternatively, the turning force may be generated manually, for example by the sonographer rotating a knob. In a preferred embodiment, the turning force is applied to the rotatable cable remotely from the transducer housing 2, although a device, such as an electric motor, alternatively may be housed within the transducer housing 2 to directly drive the gear train or the turntable base 32. Although rotation of the transducer array 4 is described herein as being brought about by the rotating cable 18 and the gear train 26, 28 and 30, one of ordinary skill in the art could devise suitable alternative rotational schemes, such as using a linear actuator to slide a cable attached to a rotatably mounted transducer array.

Preferably, the entire transducer housing 2 is formed from an acoustically transmissive material, such as a thermoplastic material. The preferred thermoplastic material is TPX™ from Mitsui Petrochemicals (America) Ltd., 250 Park Ave., Suite 950, New York, N.Y. 10177. Because the entire transducer housing 2 is formed from an acoustically transmissive material, the acoustic window 12 may be integrally formed in the transducer housing 2 by reducing the thickness of the housing 2 in the area above the transducer array 4 and lens 6. It should be noted that formation of the window 12 does not require any opening in the transducer housing 2. The window 12 and the transducer housing 2 form a continuous surface 10 adjacent to the lens 6. Accordingly, additional process steps are not required to seal the window 12 against the ingress of bodily fluids, sterilant solutions, and cleaning solutions.

The thickness of the window 12 portion of the transducer housing 2 may be constant and equal to one-half wavelength of the transmitted acoustic energy at the center frequency of the transducer array 4 in the housing material. For example, if the center frequency of the transducer array 4 is 5 MHz, the window 12 should be 0.2 mm thick, where the acoustic velocity in the thermoplastic material is assumed to be 2000 ms⁻¹.

Alternatively, the thickness of the window 12 portion of the continuous surface 10 of the transducer housing 2 may vary as a function of distance from the axis 8. For example, the window 12 may be formed into an axisymmetric converging lens by increasing the thickness of the window 12 as a function of increasing distance from the axis 8 (assuming that the velocity of sound in the housing material is greater than the velocity of sound in the body). Similarly, the window 12 may be formed into an axisymmetric diverging lens by decreasing the thickness of the window 12 as a function of increasing distance from the axis 8. Thus, to form the window 12 portion of the continuous surface 10 into a lens, the outer surface 11 of the window 12 will have a different curvature than the inner surface 13 of the window 12. With this alternative embodiment, the probe may be constructed with or without the lens 6. If the lens 6 is present, then the surface 13 of the window 12 that is adjacent to the lens 6 is formed to mate with the lens 6, and the focal length, F, of the assembly is: ##EQU1## In addition, the thickness of the window 12 portion of the continuous surface 10 may be varied to obviate reverberation artifacts that may otherwise occur if the window 12 is a constant thickness.

The thermoplastic Mitsui TPX™ material is preferred for the housing 2 because of its high modulus and low density, which provide structural rigidity and relative acoustic transparency. In addition, the high dielectric strength of the TPX™ material allows the thickness of the lens 6 to be reduced, further reducing the profile of the transducer housing 2.

The lens 6 is formed from silicone rubber, preferably Dow Corning Q5-8008 having approximately forty-two percent silicon dioxide filler. Alternatively, Dow Sylgard 577 Primerless Silicone Adhesive RTV-560 may be used, although with a slight degradation in performance.

The grease 14 provides lubrication between the stationary housing window 12 and the rotating lens 6 attached to the transducer array 4. In addition, the grease 14 displaces air that may otherwise be present between the window 12 and the lens 6. The viscosity of the grease 14 should be chosen to minimize air voids and channeling, which may otherwise occur as a result of rotating the array 4 and lens 6. Furthermore, the grease 14 should be chemically compatible with the lens 6 material and housing 2 material. Preferably, the grease 14 is made from synthetic base oils and has a low base-oil kinetic viscosity in the range of 10-40 centistokes measured at 40° C. Acceptable greases include fluorosilicone, polyalphaolefin, and fluoroether greases.

As shown in FIG. 1, the axisymmetric lens 6 may have a cylindrical side wall 44, which descends beyond the face of the transducer array 4. A recess 46, shown in FIG. 2, may be formed in the continuous surface 10 of the transducer housing 2 to mate with the shape of the lens 6. A grease seal 48 is positioned around the cylindrical wall 44 of the lens 6, as shown in FIG. 1, to contain the grease 14 to the volume between the lens 6 and the window 12. Alternatively, a seal may be integrally formed on the cylindrical wall 44 of the lens 6.

Filling ports, such as filling ports 47 and 49 as shown in FIG. 2, may be added to the transducer housing 2 to facilitate assembly, minimize air voids, and allow for addition of grease. The filling ports 47 and 49 are substantially cylindrical bores through the transducer housing 2 that are connected by a pathway to the grease-filled interface between the window 12 and the axisymmetric lens 6. A grease plug may be used to seal the filling port. The filling ports 47 and 49 facilitate assembly by providing access to the interface for either adding grease or allowing excess grease to be expelled. Due to the small volume of grease in the interface, thermally induced pressure changes could result in a loss of grease 14 through the seal 48 absent the filling ports. Air voids are minimized by providing pressure relief, under conditions of thermal expansion and contraction, to the grease-filled interface via the grease plugs, which are allowed to slide in the filling ports 47 and 49 in response to expansion or contraction of the grease.

The ultrasonic scanhead shown in FIG. 1 may be assembled by casting the lens 6 with the side wall 44 to the transducer array 4. The seal 48 is then positioned around the side wall 44 and grease 14 is applied to the lens 6 and/or the window 12. The array 4, with the previously attached lens 6, is then mated to the housing 2 by inserting the lens portion into the recess 46 and squeezing out any excess grease 14, or air voids within the grease 14, through the filling ports 47 and 49. Alternatively, the lens 6 and array 4 subassembly may be inserted into the recess 46, with the grease 14 being added after assembly through one of the filling ports 47 and 49. Excess grease 14 may exit the housing once the interface is filled through another filling port.

In another embodiment, the axisymmetric lens 6 may be secured to the recess 46 in the housing 2, in which case the lens 6 would remain stationary with the housing 2 and the transducer array 4 would rotate below the lens 6. Alternatively, the recess 46 may be removed from the transducer housing 2 and the axisymmetric lens 6 secured about its periphery to the transducer housing 2, in place of the recess 46, forming a stationary seal. In this alternative, the transducer array 4 would likewise rotate below the stationary lens 6.

The ultrasonic transducer array 4 may be excited to produce a two-dimensional image of one slice through a three-dimensional target. The plane containing the slice is referred to herein as an object plane. Focusing in one direction, herein referred to as the elevation direction, is provided by the axisymmetric lens 6. For the array and lens geometry shown in FIGS. 1 through 4, the elevation direction is the direction parallel to the long axis of the elements of the transducer array 4. Focusing in the perpendicular direction, herein referred to as the azimuthal direction, may be achieved electronically using known delay and sum techniques, such as the techniques described in U.S. Pat. Nos. 4,140,022 and 4,550,607 issued to Maslak. The azimuthal direction is perpendicular to the long axis of the elements of the transducer array 4. Azimuthal focusing provides focusing of acoustic energy at focal points within the object plane.

Because the thickness of the axisymmetric lens 6 may vary along the azimuthal direction, thereby causing some azimuthal focusing, the delay and sum technique for electronically focusing in the azimuthal direction should be modified to compensate for a lens-induced component of azimuthal focusing. The precise geometry and focusing characteristics of the axisymmetric lens are first determined. The ultrasound control and operating system can then inject compensating electronic delays by the transmitting and receiving electronics in order to account for the lens-induced component of azimuthal focusing.

Timing effects introduced by an azimuthally curved lens may be accounted for by applying Fermat's Shortest Path Law and geometric ray tracing techniques to the lens geometry and adjusting corresponding electronic delays. For a given axisymmetric lens geometry, the minimum time path from each element of the transducer array 4 through the axisymmetric lens 6 to each focal point within the object plane may be computed. For a lens in which the velocity of sound in the lens is less than the velocity of sound in the body, such as a silicone rubber lens, the minimum time path is longer for an array with a lens than it would be if there were no lens. Delay times must, therefore, be modified in both the transmit and receive circuitry to compensate for this increase in propagation time. Alternatively, the required compensating delays may be derived by applying Snell's Law and geometric ray tracing techniques to the lens geometry.

Referring now to FIG. 3, a section of the transducer array 4 and the axisymmetric lens 6 assembly is shown, the section being taken along the azimuthal direction through the center of the array. Individual transducer elements 4a . . . 4p are shown adjacent to the axisymmetric lens 6. A focal point 50 within the body is illustrated.

For a given axisymmetric lens geometry, the minimum time path from each element of the transducer array 4 through the axisymmetric lens 6 to each focal point 50 within the object plane is calculated as follows. Given a transducer element 4d centered at the point (x₁, 0) and a desired focal point 50 at (x₃, y₃), the minimum time path for the transducer elemented 4d will cross the interface between the lens 6 and the body at some point (x₂, y₂). The minimum propagation time, t, is: ##EQU2## In equation 2, B is the path length within the lens and C is the path length within the body corresponding to the minimum time path. C_(lens) and C_(body) are the velocities of sound in the lens and body, respectively.

If the axisymmetric lens 6 is a spherical lens, then the thickness, T, of the lens at the point (x₂, y₂) is: ##EQU3## In equation 3, T is the maximum thickness of the spherical lens, which is located over the center element of the array 4, and R is the radius of curvature of the lens. The equation for T(x) for a spherical lens may be approximated by the equation for T(x) for a parabolic lens: ##EQU4## Substituting for y₂, equation (2) for the minimum propagation time, t, can be rewritten as a function of the variable x₂ : ##EQU5## The coordinate x₂ that minimizes t can then be found, for example by an iterative search. Once x₂ is found for transducer element 4d, which is centered at x₁, the difference (x₂ -x₁) can be used as an initial value in the search for x₂ for neighboring transducer elements, 4c and 4e.

Knowing the value of x₂ corresponding to the minimum propagation time t for each element 4a . . . 4p of the array 4, the corresponding increase in propagation time due to the lens 6 for each element of the array 4 is: ##EQU6## where A is the distance between the transducer element and the focal point 50 at (x₃, y₃). The delay for each element of the array is determined by inputting the appropriate value of x₂. Corresponding delays must be calculated for each focal point within the object plane. Because the minimum time path is greater for an array with a lens than it is without a lens, the change in delay time, Δt, is subtracted from the delay time that the ultrasound control and operating system would apply in the absence of the axisymmetric lens to achieve azimuthal focusing. Determination of the delay time that the ultrasound control and operating system would apply in the absence of a lens is described in U.S. Pat. Nos. 4,140,022 and 4,550,607.

The transducer probe described herein may be used with an ultrasound operating and control system for scanning in a variety of scan and display formats, including, but not limited to, a variable vertex format as described in U.S. Pat. Nos. 5,148,810, 5,261,408, and 5,235,986 issued to Maslak et al., which are incorporated herein by reference. The variable vertex scan and display format provides an expanded field of view for a given transducer array geometry by transmitting ultrasonic pressure waves and receiving return echoes on a set of spatially non-overlapping acoustic scan lines, wherein each acoustic scan line originates at an arbitrary point on and at an arbitrary angle to the face of the array. The set of acoustic scan lines is formed by software control. As described in U.S. Pat. No. 5,148,810, the set of acoustic scan lines may align with rays emanating from a common vertex located a selectable distance behind the face of the transducer array. The distance between the vertex and the face of the transducer array 4 is referred to herein as the vertex offset 62.

Referring now to FIG. 4, the transducer array 4 is shown. A set of acoustic scan lines produces a field of view 52 in the variable vertex format. The set of acoustic scan lines appears to emanate from a common vertex 54. An acoustic scan line 56 from the set of acoustic scan lines is illustrated. The acoustic scan line 56 originates at a point 58 on the face of the transducer array 4 and emanates at an angle θ with respect to the normal 57 to the face of the transducer array 4. The vertex offset 62 is illustrated.

The point 58 on the face of the transducer array 4 at which the acoustic scan line 56 originates is referred to herein as the acoustic line origin. For a given transducer array geometry, the acoustic line origin is selectable under software control. The acoustic line origin for the planar array of FIG. 4 occurs on a line 59 connecting the individual transducer elements at the point corresponding approximately to the center of mass of the apodization function applied to the array 4. Thus, controlling the acoustic line origin is achieved by assigning apodization values to each element of the transducer array 4 so that the center of mass of the apodization function corresponds to the desired point 58 on the face of the transducer array 4, as described in U.S. Pat. No. 5,148,810.

In order to operate the transducer probe of FIG. 1 in the variable vertex scan and display format, the ultrasound control and operating system compensates for the presence of the axisymmetric lens 6 between the transducer array 4 and the body to be imaged. The axisymmetric lens 6 a) increases the distance between the vertex and the body to be imaged, and b) refracts the acoustic scan lines.

FIG. 5A illustrates the increased distance between the vertex 54 and the body to be imaged 60 due to the presence of the lens 6. When scanning without the lens 6, the vertex offset 62 is the distance between the vertex 54 and the face of the transducer array 4. The ultrasound control and operating system assumes, when the lens 6 is present, that the body begins at a plane 60, which is parallel to the face of the transducer array 4. The acoustic scan line 56 originates at the point 58 on the face of the transducer array 4 and at the angle θ with respect to the normal to the face of the array. The acoustic scan line 56 passes through the plane 60 at a point 66.

The ultrasound control and operating system compensates for the increase in distance between the vertex 54 and the body to be imaged by using an adjusted vertex offset 64 that accounts for the thickness of the lens 6. The vertex offset 64, which accounts for the lens 6, VA_(lens) is: ##EQU7## where VA is the vertex offset for a constant sound velocity (i.e. lens-less) medium, C_(body) is the sound velocity in the body, C_(lens) is the sound velocity in the lens 6, and T is the maximum thickness of the lens.

The presence of the lens 6 in front of the array 4 will cause the acoustic scan line to refract, thereby requiring a shift in the acoustic line origin by some distance, Δx, in the azimuthal direction. FIG. 5B is a sectional view of the transducer array 4 and the axisymmetric lens 6, the section being taken along the azimuthal direction through the array 4. An acoustic scan line 68 originates at a point 70 on the face of the transducer array 4. The acoustic scan line 68 propagates through the lens 6 to the lens/body interface at a point 72. The acoustic scan line 68 then passes through the plane 60, where imaging begins to take place, at a point 74.

The acoustic scan line 68 propagates through the lens 6 at an angle θ_(lens) with respect to a normal 76 to the face of the transducer array 4 and propagates through the body at an angle θ with respect to the normal 76. The angle of the lens/body interface at the point 72 with respect to the plane 60 is designated θ_(c).

The appropriate shift, Δx, in the acoustic line origin 70 must be computed for the acoustic scan line 68 so that the point 74, shown in FIG. 5B, coincides with the point 66, shown in FIG. 5A. The shift in acoustic line origin, Δx, must be computed for each acoustic scan line in the set of acoustic scan lines. The shift in the acoustic line origin, Δx, induced by the lens 6 may be determined as follows.

If x refers to the horizontal position of a point as measured from the center 78 of the transducer array 4, and y refers to the point's vertical position as measured from the plane 60 where imaging begins, then the horizontal position of the point 74 where the acoustic scan line 68 crosses the imaging plane 60 is:

    x.sub.74 =x.sub.66 =VA.sub.lens ·tan θ      (8)

For a spherical axisymmetric lens 6, the horizontal position of the point 72 where the acoustic scan line crosses the lens/body interface is: ##EQU8## where R is the radius of curvature of the lens 6 in the azimuthal direction. Equation (11) is arrived at by solving the quadratic equation (10) and taking the appropriate root. Equation (11) can be simplified using the approximation: ##EQU9## With this approximation, the horizontal position of the point 72 is: ##EQU10## The angle θ_(c) of the lens/body interface with respect to the imaging plane 60 at the point 72 is: ##EQU11## The angle θ_(lens) of the acoustic scan line 68 within the lens 6 with respect to the normal 76 is given by Snell's Law as: ##EQU12## Using the angle θ_(lens) the horizontal position of the acoustic line origin 70 is: ##EQU13## and the acoustic line origin shift, Δx, is:

    Δx=x.sub.70 -VA·tan θ                 (19)

The acoustic line origin shift, Δx, provides the desired point on the face of the transducer array to be equated with the center of mass of the apodization function for the transducer array.

The start-of-line delay should also be adjusted on an acoustic line-by-line basis to reduce image distortion. The start-of-line delay due to the lens 6 is the time it takes to propagate from the face of the transducer array, through the lens 6, to a plane where the ultrasound control and operating system assumes the body begins, i.e. the imaging plane 60, and back again. The ultrasound control and operating system typically assumes that the body begins at the plane that is parallel to the face of the transducer array 4 and is tangential to the lens 6.

Using the values for the acoustic line origin, the line-by-line variation in the start-of-line delay may be approximated as follows: ##EQU14## Ultrasound data acquired after the start-of-line delay are displayed by the ultrasound control and operating system, while earlier received data are discarded.

It is intended that the foregoing detailed description be regarded as illustrative rather than limiting and that it is understood that the following claims, including all equivalents, are intended to define the scope of the invention. 

We claim:
 1. An ultrasonic transducer probe, comprising:an array of ultrasonic transducers; a convex lens positioned adjacent to the array with the convex surface directed opposite to an array emission surface; an integrally formed housing encasing the array and the lens, wherein the housing has a continuous surface adjacent to the lens for passing ultrasonic energy, the continuous surface being shaped to mate with the lens, and wherein the lens is attached to the continuous surface; and a lubricating layer positioned between the lens and the array said array being rotatable with respect to said housing about an axis passing through said continuous surface.
 2. An ultrasonic transducer probe as claimed in claim is wherein the lens is axisymmetric.
 3. An ultrasonic transducer probe as claimed in claim 1, further comprising:a platform for supporting the array; a pedestal having a first end coupled to the platform and a second end coupled to a turntable base; and a gear coupled to the turntable base.
 4. An ultrasonic transducer probe as claimed in claim 3, further comprising a rotatable cable coupled to the gear.
 5. An ultrasonic transducer probe as claimed in claim 1, further comprising means for independently exciting each element of the array.
 6. An ultrasonic transducer probe as claimed in claim 5, wherein the excitation means comprises a flexible circuit electrically coupled to the array.
 7. An ultrasonic transducer probe as claimed in claim 1, further comprising a backing material upon which the array is mounted.
 8. An ultrasonic transducer probe as claimed in claim 7, wherein the backing material provides high acoustic attenuation.
 9. An ultrasonic transducer probe as claimed in claim 8, wherein the backing material comprises rigid polymeric or polymer-coated particles fused into a macroscopically rigid structure having remnant tortuous permeability to provide high acoustic attenuation and to permit fluid passage into the structure.
 10. An ultrasonic transducer probe as claimed in claim 1, wherein the continuous surface of the housing that is adjacent to the lens has a thickness of one-half wavelength of the ultrasonic energy within the housing.
 11. An ultrasonic transducer probe as claimed in claim 1, wherein the continuous surface refracts the ultrasonic energy.
 12. An ultrasonic transducer probe as claimed in claim 11, wherein the continuous surface forms an axisymmetric converging lens.
 13. An ultrasonic transducer probe as claimed in claim 1, wherein the housing comprises a thermoplastic material.
 14. An ultrasonic transducer probe as claimed in claim 1, wherein the housing has a filling port connected by a pathway to the lubricating layer.
 15. An ultrasonic transducer probe as claimed in claim 1, wherein the lens is formed from silicone rubber having 42% silicone dioxide filler.
 16. An ultrasonic transducer probe, comprising:an array of ultrasonic transducers mounted about an axis within the ultrasonic transducer probe; a convex lens mounted to rotate with the array with the convex surface directed opposite to an array emission surface, the lens being symmetric about the axis; and an integrally formed housing encasing the array and the lens, wherein an upper surface of the housing is formed into an integral window that is shaped, in a region adjacent to the lens, to mate with the lens, the housing and the lens being separated by a lubricating layer said array being rotatable with respect to said housing about said axis passing through said integral window.
 17. An ultrasonic transducer probe as claimed in claim 16, wherein the lens and the region of the housing adjacent to the lens are spherically shaped.
 18. An ultrasonic transducer probe as claimed in claim 16, wherein the housing is formed from a material that passes ultrasonic energy and the integral window has a thickness that is less than the thickness of the remainder of the housing.
 19. An ultrasonic transducer probe as claimed in claim 18, wherein the thickness of the integral window is one-half wavelength of the ultrasonic energy within the housing material.
 20. An ultrasonic transducer probe as claimed in claim 16, wherein the upper surface of the housing has a recess formed therein for encircling the lens.
 21. An ultrasonic transducer probe as claimed in claim 16, further comprising:a backing material upon which the array is mounted; a platform upon which the backing material is mounted; a pedestal having a first end that supports the platform and a second end that is coupled to a turntable base, the pedestal defining the axis; at least one gear coupled to the turntable base for rotating the base, the backing material, the array, and the lens about the axis; and a flexible circuit electrically coupled to the array.
 22. An ultrasonic transducer probe as claimed in claim 16, wherein the housing is formed from a thermoplastic material.
 23. An ultrasonic transducer probe as claimed in claim 22, wherein the thermoplastic material is acoustically transparent.
 24. An ultrasonic transducer probe as claimed in claim 16, wherein the lens further comprises a cylindrical side wall descending from the lens, wherein the side wall encircles the array.
 25. An ultrasonic transducer probe as claimed in claim 24, further comprising a lubricant seal positioned around the side wall of the lens.
 26. An ultrasonic transducer probe as claimed in claim 16, wherein the window has a thickness that varies with distance from the axis.
 27. An ultrasound system for providing diagnostic information from the interior of a body, comprising:an ultrasonic transducer probe having an array of ultrasonic transducers, a convex axisymmetric lens mounted to the array with the convex surface directed opposite to an array emission surface, and a housing encasing the array and the lens, wherein the housing has an integrally formed continuous surface adjacent to the lens, an inside of the surface being shaped to mate with the lens, the housing and the lens being separated by a lubricating layer said array being rotatable with respect to said housing about an axis passing through said continuous surface; an operating and control system for processing electrical signals produced by the ultrasonic transducer probe; and means for operatively coupling the ultrasonic transducer probe to the operating and control system.
 28. An ultrasound system as claimed in claim 27, wherein the operating and control system comprises transmitting electronics and receiving electronics, each of which have variable electronic delays for focusing the array in an azimuthal direction.
 29. An ultrasound system as claimed in claim 28, wherein at least one of the variable electronic delays compensates for azimuthal focusing induced by the axisymmetric lens.
 30. An ultrasound system as claimed in claim 27, wherein the operating and control system further comprises means for displaying acoustic echoes received by the ultrasonic transducer probe.
 31. An ultrasound system as claimed in claim 27, wherein the ultrasonic transducer probe further comprises means for rotating the array and the axisymmetric lens.
 32. An ultrasound system as claimed in claim 31, wherein the rotating means comprises an electric motor.
 33. A method of providing diagnostic information from an interior of a body, comprising:providing an ultrasound system having transmitting electronics, receiving electronics, an array of ultrasonic transducer elements having a face, and an axisymmetric lens positioned above the array, for transmitting acoustic pressure waves into the body and receiving acoustic echoes from the body through the axisymmetric lens along a set of acoustic lines; storing a value corresponding to an increase in propagation time to a focal point on an acoustic line from the set of acoustic lines due to the axisymmetric lens for at least one element of the array; and adjusting the transmitting electronics and the receiving electronics in accordance with the stored value.
 34. A method as claimed in claim 33, wherein the step of adjusting the transmitting and receiving electronics comprises adjusting a delay time provided by variable electronic delays coupled to the elements of the array.
 35. A method as claimed in claim 34, wherein the step of adjusting the delay time comprises decreasing the delay time by the stored value.
 36. A method as claimed in claim 33, wherein the set of acoustic lines is a set of spatially non-overlapping acoustic lines.
 37. A method as claimed in claim 36, wherein each acoustic line in the set of acoustic lines has an origin at a selectable point on the face of the array.
 38. A method as claimed in claim 37, wherein at least one acoustic line is refracted at an interface between the body and the axisymmetric lens.
 39. A method as claimed in claim 38, wherein each acoustic line origin is selected so that an extension of the acoustic line in the body beyond the interface passes through a substantially common vertex that is not located on the face of the array.
 40. An ultrasound system for providing diagnostic information from the interior of a body, comprising:an ultrasonic transducer probe having an array of ultrasonic transducers and an axisymmetric lens adjacent to the array; an operating and control system for processing electrical signals produced by the ultrasonic transducer probe, wherein the operating and control system comprises transmitting electronics and receiving electronics, each of which have variable electronic delays for focusing the array in an azimuthal direction, and further wherein at least one of said variable electronic delays compensates for azimuthal focusing induced by the axisymmetric lens; and means for operatively coupling the ultrasonic transducer probe to the operating and control system.
 41. An ultrasound system as claimed in claim 40, wherein the operating and control system further comprises means for acoustically scanning in a variable vertex format.
 42. An ultrasound system as claimed in claim 41, wherein the scanning means includes means for adjusting a vertex offset, an acoustic line origin, and a start-of-line delay for a set of acoustic lines to compensate for the axisymmetric lens. 